X-ray imaging system and method

ABSTRACT

An X-ray imaging system can include an X-ray source that projects a beam of X-ray radiation and an X-ray detector positioned to receive the beam of X-ray radiation at a location. The X-ray detector can include: (i) a monolithic substrate having a first side and a second side opposite the first side, (ii) a scintillation layer arranged upon the first side and including a first region and a second region, the first region having a first X-ray sensitivity and the second region having a second X-ray sensitivity different than the first X-ray sensitivity, and (iii) a photosensor array arranged upon the second side. The X-ray source and X-ray detector can be configured to adjust the location at which the X-ray detector receives the beam of X-ray radiation such that the location is primarily within the first region or the second region.

FIELD

The present disclosure relates to an X-ray imaging system and, moreparticularly, to an X-ray imaging system that provides different imagingcharacteristics with a single X-ray detector.

BACKGROUND

This section provides background information related to the presentdisclosure which is not necessarily prior art.

A subject, such as a human patient, may select or be required to undergoa surgical procedure to correct or augment an anatomy of the patient.The augmentation of the anatomy can include various procedures, such asmovement or augmentation of bone, insertion of implantable devices, orother appropriate procedures. A surgeon can perform the procedure on thesubject with images of the patient that can be acquired using imagingsystems such as a magnetic resonance imaging (MRI) system, computedtomography (CT) system, fluoroscopy (e.g., C-Arm imaging systems), orother appropriate imaging systems.

Images of a patient can assist a surgeon in performing a procedureincluding planning the procedure and performing the procedure. A surgeonmay select a two dimensional image or a three dimensional imagerepresentation of the patient. The images can assist the surgeon inperforming a procedure with a less invasive technique by allowing thesurgeon to view the anatomy of the patient without removing theoverlying tissue (including dermal and muscular tissue) when performinga procedure.

SUMMARY

This section provides a general summary of the disclosure, and is not acomprehensive disclosure of its full scope or all of its features.

According to various embodiments, an X-ray imaging system can include anX-ray source that projects a beam of X-ray radiation and an X-raydetector positioned to receive the beam of X-ray radiation at alocation. The X-ray detector can include: (i) a monolithic substratehaving a first side and a second side opposite the first side, (ii) ascintillation layer arranged upon the first side and including a firstregion and a second region, the first region having a first X-raysensitivity and the second region having a second X-ray sensitivitydifferent than the first X-ray sensitivity, and (iii) a photosensorarray arranged upon the second side. The X-ray source and X-ray detectorcan be configured to adjust the location at which the X-ray detectorreceives the beam of X-ray radiation such that the location is primarilywithin the first region or the second region.

An imaging method for use with an X-ray imaging system can includepositioning a patient between an X-ray source configured to project abeam of X-ray radiation and an X-ray detector to receive the beam ofX-ray radiation at a location. The X-ray detector can include: (i) amonolithic substrate having a first side and a second side opposite thefirst side, (ii) a scintillation layer arranged upon the first side andincluding a first region and a second region, the first region having afirst X-ray sensitivity and the second region having a second X-raysensitivity different than the first X-ray sensitivity, and (iii) aphotosensor array arranged upon the second side. The method can furtherinclude adjusting the location to correspond to a region of interest ofthe patient to be imaged such that at least a portion of the beam ofX-ray radiation passes through the region of interest and impingesprimarily on the first region. Additionally, the method can includeimaging the patient to generate an image having a first image qualityfor the region of interest of the patient and a second image quality fora portion of the patient other than the region of interest, the firstimage quality corresponding to the first region and the second imagequality corresponding to the second region.

An X-ray imaging system can include an X-ray source that projects a beamof X-ray radiation, an X-ray detector positioned to receive the beam ofX-ray radiation at a location and a computing system coupled to theX-ray source and X-ray detector. The X-ray detector can include: (i) amonolithic substrate having a first side and a second side opposite thefirst side, (ii) a scintillation layer arranged upon the first side andincluding a first region and a second region, the first region having afirst X-ray sensitivity and the second region having a second X-raysensitivity different than the first X-ray sensitivity, and (iii) aphotosensor array arranged upon the second side. The computing systemcan be configured to generate an image of a patient that is imaged bythe X-ray source and X-ray generator. The computing system can include adisplay device configured to display the image of the patient. Thecomputing system can be further configured to adjust the location tocorrespond to a region of interest of the patient such that at least aportion of the beam of X-ray radiation is configured to pass through theregion of interest and impinge primarily on the first region. The imageof the patient can have a first image quality for the region of interestof the patient and a second image quality for a portion of the patientother than the region of interest. The first image quality cancorrespond to the first region and the second image quality cancorrespond to the second region.

Further areas of applicability will become apparent from the descriptionprovided herein. The description and specific examples in this summaryare intended for purposes of illustration only and are not intended tolimit the scope of the present disclosure.

DRAWINGS

The drawings described herein are for illustrative purposes only ofselected embodiments and not all possible implementations, and are notintended to limit the scope of the present disclosure.

FIG. 1 is an environmental view of an exemplary imaging system accordingto various embodiments of the present disclosure in an operatingtheatre;

FIG. 2 is a schematic illustration of an exemplary computing system ofthe imaging system of FIG. 1;

FIG. 3 is a schematic illustration of an exemplary system unit of thecomputing system of FIG. 2;

FIG. 4 is a schematic illustration of an exemplary X-ray detector of theimaging system of FIG. 1;

FIG. 5 is a schematic cross-sectional view of the exemplary X-raydetector of FIG. 4 taken along the line 5-5;

FIG. 6 is a schematic cross-sectional view of the exemplary X-raydetector of FIG. 4 taken along the line 5-5 showing an alternateconstruction;

FIG. 7 is a schematic illustration of an exemplary X-ray source and anexemplary X-ray detector of the imaging system of FIG. 1;

FIG. 8A is a schematic illustration of an exemplary X-ray detector ofthe imaging system of FIG. 1 with the location of a beam of X-rayradiation in a first position;

FIG. 8B is a schematic illustration of an exemplary X-ray detector ofthe imaging system of FIG. 1 with the location of a beam of X-rayradiation in a second position;

FIG. 9 is a schematic illustration of an exemplary X-ray detector of theimaging system of FIG. 1; and

FIG. 10 is a schematic illustration of an exemplary X-ray detector ofthe imaging system of FIG. 1.

DETAILED DESCRIPTION

The following description is merely exemplary in nature. It should beunderstood that throughout the drawings, corresponding referencenumerals indicate like or corresponding parts and features. As indicatedabove, the present teachings are directed toward an imaging system, suchas an O-Arm® imaging system sold by Medtronic Navigation, Inc. having aplace of business in Louisville, Colo., USA. It should be noted,however, that the present teachings could be applicable to anyappropriate imaging device, such as a C-arm imaging device. Further, asused herein, the term “module” can refer to a computer readable mediathat can be accessed by a computing device, an application specificintegrated circuit (ASIC), an electronic circuit, a processor (shared,dedicated, or group) and memory that executes one or more software orfirmware programs, a combinational logic circuit, and/or other suitablesoftware, firmware programs or components that provide the describedfunctionality.

With reference to FIG. 1, in an operating theatre or operating room 10,a user, such as a user 12, can perform a procedure on a patient 14. Inperforming the procedure, the user 12 can use an imaging system 16 toacquire image data of the patient 14 for performing a procedure. Theimage data acquired of the patient 14 can include two-dimension (2D)projections acquired with an X-ray imaging system, including thosedisclosed herein. It will be understood, however, that 2D forwardprojections of a volumetric model can also be generated, also asdisclosed herein.

In one example, a model can be generated using the acquired image data.The model can be a three-dimension (3D) volumetric model generated basedon the acquired image data using various techniques, including algebraiciterative techniques, also as discussed further herein. Displayed imagedata 18 can be displayed on a display device 20, and additionally, couldbe displayed on a display device 32 a associated with an imagingcomputing system 32, as will be discussed in greater detail herein. Thedisplayed image data 18 can be a 2D image, a 3D image, or a timechanging four-dimension image. The displayed image data 18 can alsoinclude the acquired image data, the generated image data, both, or amerging of both the types of image data.

It will be understood that the image data acquired of the patient 14 canbe acquired as 2D projections, for example with an X-ray imaging system.The 2D projections can then be used to reconstruct the 3D volumetricimage data of the patient 14. Also, theoretical or forward 2Dprojections can be generated from the 3D volumetric image data.Accordingly, it will be understood that image data can be either or bothof 2D projections or 3D volumetric models.

The display device 20 can be part of a computing system 22. Thecomputing system 22 can include a variety of computer-readable media.The computer-readable media can be any available media that can beaccessed by the computing system 22 and can include both volatile andnon-volatile media, and removable and non-removable media. By way ofexample, and not limitation, the computer-readable media can comprisecomputer storage media and communication media. Storage media includes,but is not limited to, RAM, ROM, EEPROM, flash memory or other memorytechnology, CD-ROM, Digital Versatile Disk (DVD) or other optical diskstorage, magnetic cassettes, magnetic tape, magnetic disk storage orother magnetic storage devices, or any other medium which can be used tostore computer-readable instructions, software, data structures, programmodules, and other data and which can be accessed by the computingsystem 22. The computer-readable media may be accessed directly orthrough a network such as the Internet.

In one example, the computing system 22 can include an input device 24,such as a keyboard, and one or more processors 26 (the one or moreprocessors can include multiple-processing core processors,microprocessors, etc.) that can be incorporated with the computingsystem 22. The input device 24 can comprise any suitable device toenable a user to interface with the computing system 22, such as atouchpad, touch pen, touch screen, keyboard, mouse, joystick, trackball,wireless mouse, audible controls or a combination thereof. Furthermore,while the computing system 22 is described and illustrated herein ascomprising the input device 24 discrete from the display device 20, thecomputing system 22 could comprise a touchpad or tablet computingdevice, and further, that the computing system 22 could be integratedwithin or be part of the imaging computing system 32 associated with theimaging system 16.

A connection 28 can be provided between the computing system 22 and thedisplay device 20 for data communication to allow driving the displaydevice 20 to illustrate the image data 18.

The imaging system 16 can include the O-Arm® imaging system sold byMedtronic Navigation, Inc. having a place of business in Louisville,Colo., USA. It should be noted, however, that the present teachingscould be applicable to any appropriate imaging device, such as a C-armimaging device. The imaging system 16, including the O-Arm® imagingsystem, or other appropriate imaging systems in use during a selectedprocedure are also described in U.S. patent application Ser. No.12/465,206, entitled “System And Method For Automatic RegistrationBetween An Image And A Subject,” filed on May 13, 2009, incorporatedherein by reference in its entirety. Additional description regardingthe O-Arm imaging system or other appropriate imaging systems can befound in U.S. Pat. Nos. 7,188,998, 7,108,421, 7,106,825, 7,001,045 and6,940,941, each of which is incorporated herein by reference in theirentirety.

The imaging system 16 can include a mobile cart 30 that includes theimaging computing system 32 and an imaging gantry 34 in which ispositioned an X-ray source 36 and an X-ray detector 100. With referenceto FIG. 1, the mobile cart 30 can be moved from one operating theater orroom to another and the gantry 34 can move relative to the mobile cart30, as discussed further herein. This allows the imaging system 16 to bemobile so that it can be used in multiple locations and with multipleprocedures without requiring a capital expenditure or space dedicated toa fixed imaging system.

With reference to FIG. 2, a diagram is provided that illustrates anexemplary embodiment of the imaging computing system 32, some or all ofthe components of which can be used in conjunction with the teachings ofthe present disclosure. The imaging computing system 32 can include avariety of computer-readable media. The computer-readable media can beany available media that can be accessed by the imaging computing system32 and includes both volatile and non-volatile media, and removable andnon-removable media. By way of example, and not limitation, thecomputer-readable media can comprise computer storage media andcommunication media. Storage media includes, but is not limited to, RAM,ROM, EEPROM, flash memory or other memory technology, CD-ROM, DigitalVersatile Disk (DVD) or other optical disk storage, magnetic cassettes,magnetic tape, magnetic disk storage or other magnetic storage devices,or any other medium which can be used to store computer-readableinstructions, software, data structures, program modules, and other dataand which can be accessed by the imaging computing system 32. Thecomputer-readable media may be accessed directly or through a networksuch as the Internet.

In one example, the imaging computing system 32 comprises a displaydevice 32 a and a system unit 32 b. As illustrated, the display device32 a can comprise a computer video screen or monitor. The imagingcomputing system 32 can also include at least one input device 32 c. Thesystem unit 32 b includes, as shown in FIG. 3, a processor 92 and amemory 94, which can include software 96 and data 98.

In this example, the at least one input device 32 c comprises akeyboard. It should be understood, however, that the at least one inputdevice 32 c can comprise any suitable device to enable a user tointerface with the imaging computing system 32, such as a touchpad,touch pen, touch screen, keyboard, mouse, joystick, trackball, wirelessmouse, audible controls or a combination thereof. Furthermore, while theimaging computing system 32 is described and illustrated herein ascomprising the system unit 32 b with the display device 32 a, theimaging computing system 32 could comprise a touchpad or a tabletcomputing device, and the display could employ the display 20.

The imaging computing system 32 can control the source 36, the detector100 and rotor 40 to enable off-center image data acquisition. Aconnection can be provided between the processor 92 and the displaydevice 32 a for data communication to allow driving the display device32 a to illustrate the image data 18.

With reference to FIG. 1, the source 36 can emit a beam of X-rayradiation through the patient 14 to be detected by the detector 100. Asis understood by one skilled in the art, the X-rays emitted by thesource 36 can be emitted in a cone and detected by the detector 100. Thesource 36 and the detector 100 can each be coupled to a rotor 40 so asto be generally diametrically opposed within the gantry 34, and movablewithin the gantry 34 about the patient 14. Thus, the detector 100 canmove rotationally in a 360° motion around the patient 14 generally inthe directions of arrow 39, and the source 36 can move in concert withthe detector 100 such that the source 36 remains generally 180° apartfrom and opposed to the detector 100.

In addition, the source 36 can be pivotably mounted to the rotor 40 andcontrolled by an actuator, such that the source 36 can be controllablypivoted relative to the rotor 40 and the detector 100. By controllablypivoting the source 36, the trajectory of the X-rays can be angled oraltered relative to the patient 14, without requiring the patient 14 tobe repositioned relative to the gantry 34. Further, the detector 100 cantranslate about an arc relative to the rotor 40. As the detector 100 cantranslate, the detector 100 can detect the X-rays emitted by the source36 at any desired pivot angle, which can enable the acquisition ofoff-center image data. The rotor 40 can be rotatable about the gantry 34as needed to acquire the desired image data (on center or off-center).Additional details regarding the mechanics of the movement of the source36, detector 100 and rotor 40 are disclosed in U.S. Pat. No. 7,108,421,which was previously incorporated by reference above, and U.S. PatentApplication No. 7,108,421, filed concurrently herewith, entitled “SYSTEMAND METHOD FOR OFF-CENTER IMAGING” to Helm et al., which is incorporatedherein by reference in its entirety.

With reference to FIG. 1, the gantry 34 can isometrically sway or swing(herein also referred to as iso-sway) generally in the direction ofarrow 41, relative to the patient 14, which can be placed on a patientsupport or table 15. The gantry 34 can also tilt relative to the patient14 illustrated by arrows 42, move longitudinally along the line 44relative to the patient 14 and the mobile cart 30, can move up and downgenerally along the line 46 relative to the mobile cart 30 andtransversely to the patient 14, and move perpendicularly generally inthe direction of arrow 48 relative to the patient 14 to allow forpositioning of the source 36/detector 100 relative to the patient 14.

The imaging system 16 can be precisely controlled by the imagingcomputing system 32 to move the source 36/detector 100 relative to thepatient 14 to generate precise image data of the patient 14. Inaddition, the imaging system 16 can be connected with the processor 26via connection 50 which can include a wired or wireless connection orphysical media transfer from the imaging system 16 to the processor 26.Thus, image data collected with the imaging system 16 can also betransferred from the imaging computing system 32 to the computing system22 for navigation, display, reconstruction, etc.

Briefly, with continued reference to FIG. 1, according to variousembodiments, the imaging system 16 can be used with an unnavigated ornavigated procedure. In some embodiments, the imaging system 16 can beintegrated with a navigation system 17 for performing a navigatedprocedure. The navigation system 17 can include, e.g., the computingsystem 22, an optical localizer 60, an electromagnetic localizer 62, adynamic reference frame 64, an instrument 66, an optical tracking device68, an electromagnetic tracking device 70, at least one communicationline 72, 78, 80, and/or a navigation interface device 74, as furtherdescribed below. In a navigated procedure, a localizer, including eitheror both of an optical localizer 60 and an electromagnetic localizer 62can be used to generate a field or receive or send a signal within anavigation domain relative to the patient 14. The navigated space ornavigational domain relative to the patient 14 can be registered to theimage data 18 to allow registration of a navigation space defined withinthe navigational domain and an image space defined by the image data 18.A patient tracker or a dynamic reference frame 64 can be connected tothe patient 14 to allow for a dynamic registration and maintenance ofregistration of the patient 14 to the image data 18.

An instrument 66 can then be tracked relative to the patient 14 to allowfor a navigated procedure. The instrument 66 can include an opticaltracking device 68 and/or an electromagnetic tracking device 70 to allowfor tracking of the instrument 66 with either or both of the opticallocalizer 60 or the electromagnetic localizer 62. The instrument 66 caninclude a communication line 72 with a navigation interface device 74,which can communicate with the electromagnetic localizer 62 and/or theoptical localizer 60. Using the communication lines 72, 78 respectively,the navigation interface device 74 can then communicate with theprocessor 26 with a communication line 80. It will be understood thatany of the connections or communication lines 28, 50, 76, 78, or 80 canbe wired, wireless, physical media transmission or movement, or anyother appropriate communication. Nevertheless, the appropriatecommunication systems can be provided with the respective localizers toallow for tracking of the instrument 66 relative to the patient 14 toallow for illustration of the tracked location of the instrument 66relative to the image data 18 for performing a procedure.

It will be understood that the instrument 66 can be an interventionalinstrument and/or an implant. Implants can include a ventricular orvascular stent, a spinal implant, neurological stent or the like. Theinstrument 66 can be an interventional instrument such as a deep brainor neurological stimulator, an ablation device, or other appropriateinstrument. Tracking the instrument 66 allows for viewing the locationof the instrument 66 relative to the patient 14 with use of theregistered image data 18 by superimposing an icon/indicia of theinstrument 66 on the image data 18 and without direct viewing of theinstrument 66 within the patient 14.

Further, the imaging system 16 can include a tracking device, such as anoptical tracking device 82 or an electromagnetic tracking device 84 tobe tracked with a respective optical localizer 60 or the electromagneticlocalizer 62. The tracking device 82, 84 can be associated directly withthe source 36, the detector 100, rotor 40, the gantry 34, or otherappropriate part of the imaging system 16 to determine the location orposition of the source 36, detector 100, rotor 40 and/or gantry 34relative to a selected reference frame. As illustrated, the trackingdevice 82, 84 can be positioned on the exterior of the housing of thegantry 34. Accordingly, the imaging system 16 can be tracked relative tothe patient 14 as can the instrument 66 to allow for initialregistration, automatic registration or continued registration of thepatient 14 relative to the image data 18. Registration and navigatedprocedures are discussed in the above incorporated U.S. patentapplication Ser. No. 12/465,206.

Referring now to FIGS. 4 and 5, an exemplary X-ray detector 100according to some embodiments of the present disclosure is illustrated.Detector 100 includes a substrate 110, a scintillation layer 120 and aphotosensor array 130 (such as a thin-film transistor, photodiode orsimilar). During operation of the imaging system 16, the X-ray source 36will project a beam of X-ray radiation towards the X-ray detector 100.The scintillation layer 120 will convert the X-ray radiation intoradiation at a different wavelength, such as visible light. The visiblelight will travel through the substrate 110 and be detected by thephotosensor array 130. The photosensor array will convert the visiblelight into an electrical signal that can be detected and utilized by thecomputing system 32 to generate an image (such as displayed image data18) of the patient 14.

The substrate 110 can have a first side 112 and a second side 114opposite the first side 112. The substrate 110 can be a monolithicsubstrate made of glass or similar material. The monolithic constructionof substrate 110 can reduce the amount of unintended distortion(scattering, reflection, refraction, diffraction, etc.) of the visiblelight generated by the scintillation layer 120.

The scintillation layer 120 can be arranged on the first side 112 of thesubstrate 110. In various embodiments, the scintillation layer 120 canbe manufactured by depositing a scintillation material on the substrate110, e.g., by physical vapor deposition, sputter deposition or otherdeposition technique. Examples of scintillation material include cesiumiodide (CsI) and terbium doped gadolinium oxysulfide (Gd₂O₂S:Tb).

In some embodiments of the present disclosure, the X-ray detector 100can include regions that have different X-ray sensitivities, e.g., byutilizing different scintillation materials for each region and/orvarying the thickness of a single scintillation material across regions.In the illustrated example, the scintillation layer 120 includes a firstregion 122 having a first X-ray sensitivity and a second region 124having a different second X-ray sensitivity. The first region 122 has afirst thickness t1 of scintillation material and the second region 124has a second thickness t2 of scintillation material that is differentthan the first thickness t1. The differing X-ray sensitivities of thefirst and second regions 122, 124 allow a user 12 to utilize the imagingsystem 16 to generate image data having different imagingcharacteristics/image qualities, as described below. While theillustrated example shows an X-ray detector 100 with a scintillationlayer 120 that includes two different regions that are arrangedside-by-side, it will be appreciated any number of regions greater thanor equal to two may be utilized with the present disclosure.Additionally, the regions 122, 124 may be arranged other thanside-by-side (e.g., an X-ray detector 100′ having regions 122′, 124′,where the inner region 122′ is surrounded by one or more outer regions124′, or an X-ray detector 100″ having regions 122″, 124″, where theregion 122″ is confined to a corner portion 125 of the X-ray detector100″, etc.) without departing from the scope of the present disclosure.The X-ray detectors 100′, 100″ are shown in FIGS. 9-10.

The photosensor array 130 can be arranged upon the second side 114 ofthe substrate 110. The photosensor array 130 can be bonded to the secondside 114, e.g., by adhesive or other bonding material. In someembodiments, the photosensor array 130 can be composed of a plurality ofmonolithic photosensor sub-arrays arranged next to each other. Forexample, referring now to FIG. 6, the photosensor array 130′ can includea first monolithic photosensor sub-array 132 and a second monolithicphotosensor sub-array 134 bonded together at a junction 135.

In the illustrated example of FIG. 6, the first monolithic photosensorsub-array 132 corresponds to the first region 122 and the secondmonolithic photosensor sub-array 134 corresponds to the second region124. In this manner, the first monolithic photosensor sub-array 132 canreceive the radiation generated by the first region 122 and the secondmonolithic photosensor sub-array 134 can receive the radiation generatedby the second region 124. Further, in some embodiments each of themonolithic photosensor sub-arrays 132, 134 can have a different set ofperformance parameters. The performance parameters for each of themonolithic photosensor sub-arrays 132, 134 can be chosen to correspondto the X-ray sensitivity of its associated region 122, 124. For exampleonly, the first monolithic photosensor sub-array 132 can have a firstset of performance parameters to correspond to the first X-raysensitivity of the first region 122 and the second monolithicphotosensor sub-array 134 can have a second set of performanceparameters to correspond to the second X-ray sensitivity of the secondregion 124. The term “performance parameters” throughout thisdescription can include, but is not limited to, the responsivity, darkcurrent, noise-equivalent power, linearity of output, spectral response,quantum efficiency, light sensitivity, and/or response time of aphotosensor array.

In some embodiments of the present disclosure, the X-ray source 36 caninclude one or more filters (FIG. 7) arranged to filter the beam ofX-ray radiation projected from the X-ray source 36. The filter(s) can beutilized to adapt the beam of X-ray radiation projected from the X-raysource 36 to correspond to the X-ray sensitivities of the regions 122,124 of the X-ray detector 100 and/or the sets of performance parametersof the photosensor sub-arrays 132, 134 in order to improve the imagingcharacteristics/image quality of the image data. For example only, theX-ray source 36 can include a first filter 170 arranged to filter thebeam of X-ray radiation received at the first region 122 of the X-raydetector 100 and a second filter 172 arranged to filter the beam ofX-ray radiation received at the second region 124. The first filter 170can have a first set of filtering characteristics and the second filter172 can have a second set of filtering characteristics different thanthe first set. The term “filtering characteristics” throughout thisdescription can include, but is not limited to, the frequencies and/orenergy level(s) filtered out by a filter.

During operation of the imaging system 16, the X-ray source 36 projectsa beam of X-ray radiation towards the X-ray detector 100 that has beenpositioned to receive the beam of X-ray radiation. The position of theX-ray source 36 and/or the X-ray detector 100 can be adjusted relativeto one another in order to adjust the location 150 on the X-ray detector100 that receives the beam of X-ray radiation. For examples, the beam ofX-ray radiation can be received upon the entirety of the X-ray detector100. Alternatively, the beam of X-ray radiation can be received upononly a portion of the X-ray detector 100. The user 12 can adjust, e.g.,via computing system 32, the location 150 at which the X-ray detector100 receives the beam of X-ray radiation based on the imagingcharacteristics/image quality desired by the user 12. The term “imagingcharacteristics” and/or “image quality” throughout this description caninclude, but are not limited to, varying levels of contrast, contrastsensitivity, dose efficiency, dose to patient, noise, artifacts, and/ordistortion.

In some embodiments, the X-ray source 36 and X-ray detector 100 can beadjusted such that the location 150 at which the X-ray detector 100receives the beam of X-ray radiation is primarily within either thefirst region 122 (FIG. 8A) or second region 124 (FIG. 8B). In thisapplication, a location that receives a beam of X-ray radiation isconsidered to be received “primarily” within a region if more than 50%of the location is within that region. In some embodiments, the X-raysource 36 and X-ray detector 100 can be adjusted such that the location150 at which the X-ray detector 100 receives the beam of X-ray radiationis more than 70%, more than 90% or entirely within either the first orsecond region 122, 124. In this manner, the imaging system 16 can takeadvantage of the different X-ray sensitivities of the first and secondregions 122, 124 to image the patient 14. For example only, imaging lowcontrast regions of interest of a patient 14 (such as the soft tissue ofthe brain) may require substantially different imagingcharacteristics/image quality than imaging high contrast regions (suchas bone). With the present imaging system 16, the user 12 may utilizedifferent regions (first region 122 or second region 124) of the X-raydetector 100 depending on the region of interest (soft tissue, bone,etc.) of the patient 14 to be imaged in order to provide the appropriateimaging characteristics/image quality for the image data.

No matter what type of tissue (bony structure, soft tissue, etc.) to beimaged, the imaging system 16 can be utilized to generate image datawith the appropriate imaging characteristics and/or image quality. Theimaging system 16 (such as X-ray source 36 and/or X-ray detector 100)can be adjusted to adjust the location 150 to be primarily within one ofthe regions 122, 124 of the X-ray detector 100 depending on which region(122, 124) has the appropriate X-ray sensitivity for the subject ofinterest. For example, a region of interest 160 of the patient 14 can bepositioned such that at least a portion of the beam of X-ray radiationpasses through the region of interest 160 and impinges on the desiredregion 122, 124. In this manner, the patient 14 can be imaged togenerate image data that has a first image quality (corresponding to oneof the first and second regions 122, 124) for the region of interest 160and a second image quality (corresponding to the other one of the firstand second regions 122, 124) for a portion 165 of the patient 14 otherthan the region of interest 160.

An exemplary method of operating an X-ray imaging system, such asimaging system 16, according to various embodiments of the presentdisclosure can include providing an X-ray source 36 that is configuredto project a beam of X-ray radiation. An X-ray detector 100 (asdescribed above) can be positioned to receive the beam of X-rayradiation at a location 150. The method can also include adjusting thelocation 150 to correspond to a region of interest 160 of a patient 14to be imaged. The location 150 can be adjusted such that at least aportion of the beam of X-ray radiation passes through the region ofinterest 160 and impinges primarily on, for example only, the firstregion 122. The patient 14 can be imaged to generate an image (such asdisplayed image data 18) of the patient 14. The image can have a firstimage quality for the region of interest 160 of the patient 14 and asecond image quality for a portion of the patient 14 other than theregion of interest 160. The first image quality can correspond to thefirst region 122 and the second image quality can correspond to thesecond region 124.

While specific examples have been described in the specification andillustrated in the drawings, it will be understood by those of ordinaryskill in the art that various changes can be made and equivalents can besubstituted for elements thereof without departing from the scope of thepresent teachings. Furthermore, the mixing and matching of features,elements and/or functions between various examples is expresslycontemplated herein so that one of ordinary skill in the art wouldappreciate from the present teachings that features, elements and/orfunctions of one example can be incorporated into another example asappropriate, unless described otherwise, above. Moreover, manymodifications can be made to adapt a particular situation or material tothe present teachings without departing from the essential scopethereof. Therefore, it is intended that the present teachings not belimited to the particular examples illustrated by the drawings anddescribed in the specification, but that the scope of the presentteachings will include any embodiments falling within the foregoingdescription.

What is claimed is:
 1. An X-ray imaging system comprising: a rotorconfigured to rotate about an object; an X-ray source that projects abeam of X-ray radiation, wherein the beam is a cone beam, and the X-raysource is mounted on the rotor and is configured to project the beam ofX-ray radiation towards the object; and an X-ray detector is mounted onthe rotor and positioned to receive the beam of X-ray radiation at alocation and after passing through the object, wherein the X-raydetector includes: a single monolithic substrate having a first side anda second side opposite the first side, a single scintillation layerarranged upon the first side and including a first region and a secondregion, wherein the first region is configured to have a first X-raysensitivity, and wherein the second region is configured to have asecond X-ray sensitivity different than the first X-ray sensitivity, anda photosensor array arranged upon the second side, wherein the X-raysource and the X-ray detector are configured to adjust the location atwhich the X-ray detector receives the beam of X-ray radiation such thatthe location is at least partially within the first region or the secondregion, either (a) in a plane, the first region is completely surroundedby the second region, or (b) the first region is confined to only asingle corner portion of the X-ray detector, the X-ray source isconfigured to pivot relative to the rotor and the X-ray detector betweena first position and a second position to adjust the location at whichthe X-ray detector receives the beam of X-ray radiation, when the X-raysource is pivoted to the first position, a majority of the location iswithin the first region, and when the X-ray source is pivoted to thesecond position, a majority of the location is within the second region.2. The X-ray imaging system of claim 1, wherein the single monolithicsubstrate comprises glass.
 3. The X-ray imaging system of claim 1,wherein the X-ray source and the X-ray detector are configured to adjustthe location at which the X-ray detector receives the beam of X-rayradiation such that the location is entirely within the first region orthe second region.
 4. The X-ray imaging system of claim 1, wherein: thesingle scintillation layer includes a scintillation material; and thescintillation material is disposed on the single monolithic substrate.5. The X-ray imaging system of claim 1, wherein: the first region has afirst thickness of scintillation material to provide the first X-raysensitivity; the second region has a second thickness of scintillationmaterial; and the second thickness is different than the first thicknessto provide the second X-ray sensitivity.
 6. The X-ray imaging system ofclaim 5, wherein: the single scintillation layer includes thescintillation material; and the scintillation material is disposed onthe single monolithic substrate.
 7. The X-ray imaging system of claim 1,wherein the X-ray source includes: a first filter arranged to filter thebeam of X-ray radiation prior to being received at the first region; anda second filter arranged to filter the beam of X-ray radiation prior tobeing received at the second region, wherein the first filter has afirst set of filtering characteristics, and wherein the second filterhas a second set of filtering characteristics different than the firstset of filtering characteristics.
 8. The X-ray imaging system of claim1, further comprising a navigation system connected to the X-ray sourceand the X-ray detector.
 9. The X-ray imaging system of claim 1, wherein,in the plane, the first region is completely surrounded by the secondregion.
 10. The X-ray imaging system of claim 1, wherein, in the plane,the first region is confined to only the single corner portion of theX-ray detector.
 11. The X-ray imaging system of claim 1, wherein allportions of the single scintillation layer having the first x-raysensitivity are confined to the single corner portion of the X-raydetector.
 12. An X-ray imaging system comprising: a rotor configured torotate about an object; an X-ray source mounted on the rotor andconfigured to project a beam of X-ray radiation towards the object,wherein the beam is a cone beam; and an X-ray detector mounted on therotor and positioned to receive the beam of X-ray radiation at alocation and after passing through the object, wherein the X-raydetector includes: a single monolithic substrate having a first side anda second side opposite the first side, a single scintillation layerarranged upon the first side and including a first region and a secondregion, wherein the first region is configured to have a first X-raysensitivity, and wherein the second region is configured to have asecond X-ray sensitivity different than the first X-ray sensitivity, anda photosensor array arranged upon the second side, wherein the X-raysource is configured to pivot relative to the rotor and the X-raydetector between a first position and a second position to adjust thelocation at which the X-ray detector receives the beam of X-rayradiation, when the X-ray source is pivoted to the first position, amajority of the location is within the first region, and when the X-raysource is pivoted to the second position, a majority of the location iswithin the second region.